Intraocular lenses

ABSTRACT

A refractive intraocular lens including an optic portion having an outer peripheral edge and two or more but preferably two balanced opposed looped haptic elements. Each looped haptic element is formed to have two broad connecting portions, two radial orientation portions, two spring portions and a linking portion for supporting the optic portion in a patient&#39;s eye. The two broad connecting portions of each looped haptic element is permanently connected to the outer peripheral edge of the optic portion. Each looped haptic element is likewise formed to have greater resistance to bending in a plane generally parallel to an eye&#39;s optical axis than in a plane generally perpendicular to the eye&#39;s optical axis. The intraocular lens is so designed to exhibit less than approximately 1.0 mm axial displacement or tilting of the optic portion along the eye&#39;s optical axis under a compression force suitable to effect a 1.0 mm in diameter compression in overall length of the intraocular lens.

FIELD OF THE INVENTION

The present invention relates to intraocular lenses (IOLs) and a methodfor making and using the same. More particularly, the present inventionrelates to IOLs designed primarily for refractive correction in aphakiceyes. IOLs made in accordance with the present invention are used inaphakic eyes to replace a surgically removed diseased natural lens, suchas in the case of cataracts. IOLs made in accordance with the presentinvention may also be used in phakic eyes in conjunction with a naturallens to correct vision impairments.

BACKGROUND OF THE INVENTION

IOL implants have been used for years in aphakic eyes as replacementsfor diseased natural crystalline lenses that have been surgicallyremoved from the eyes. Many different IOL designs have been developedover past years and proven successful for use in aphakic eyes. Thesuccessful IOL designs to date primarily include an optic portion withsupports therefor, called haptics, connected to and surrounding at leastpart of the optic portion. The haptic portions of an IOL are designed tosupport the optic portion of the IOL in the lens capsule or posteriorchamber of an eye when used in aphakic eyes or in the posterior oranterior chamber of an eye when used in phakic eyes.

Commercially successful IOLs have been made from a variety ofbiocompatible materials, ranging from more rigid materials such aspolymethylmethacrylate (PMMA) to softer, more flexible materials capableof being folded or compressed such as silicones, certain acrylics, andhydrogels. Haptic portions of the IOLs have been formed separately fromthe optic portion and later connected thereto through processes such asheat, physical staking and/or chemical bonding. Haptics have also beenformed as an integral part of the optic portion in what is commonlyreferred to as “single-piece” IOLs.

Softer, more flexible IOLs have gained in popularity in more recentyears due to their ability to be compressed, folded, rolled or otherwisedeformed. Such softer IOLs may be deformed prior to insertion thereofthrough an incision in the cornea of an eye. Following insertion of theIOL in an eye, the IOL returns to its original pre-deformed shape due tothe memory characteristics of the soft material. Softer, more flexibleIOLs as just described may be implanted into an eye through an incisionthat is much smaller, i.e., 2.8 to 3.2 mm, than that necessary for morerigid IOLs, i.e., 4.8 to 6.0 mm. A larger incision is necessary for morerigid IOLs because the lens must be inserted through an incision in thecornea slightly larger than the diameter of the inflexible IOL opticportion. Accordingly, more rigid IOLs have become less popular in themarket since larger incisions have been found to be associated with anincreased incidence of postoperative complications, such as inducedastigmatism.

After IOL implantation in either phakic or aphakic applications, bothsofter and more rigid IOLs are subject to compressive forces exerted onthe outer edges thereof, which typically occur when an individualsquints or rubs the eye. These compressive forces may result indecentration of the IOL and distortion of the visual image. Compressiveforces exerted on an IOL also tend to cause the lens to tilt or haveaxial displacement of the IOL along the optical axis of an eye. Movementof an IOL along the optical axis of an eye has the potential to causethe IOL to contact and damage delicate eye tissues. Also, IOLs ofcurrent designs, whether formed of either softer or more rigidmaterials, tend to deflect along the optical axis of an eye when thehaptics are compressed. IOL manufacturers provide a wide range of IOLsizes to more precisely fit IOLs to each particular patient's eye size.Providing a wide range of IOL sizes is an attempt to minimize thepotential for axial displacement of the IOL along the optical axis of aneye.

Because of the noted shortcomings of current IOL designs, there is aneed for IOLs designed to minimize tilt or axial displacement of the IOLoptic portion along the optical axis of the eye when compressive forcesare exerted against the outer edges thereof. By lessening an IOL'smovement along the optical axis of an eye, more certain refractivecorrection may be achieved and the risk of tissue damage may be reduced.

SUMMARY OF THE INVENTION

An intraocular lens (IOL) made in accordance with the present inventionhas an optic portion with an outer peripheral edge and two, three orfour, but preferably two, looped haptic elements for supporting theoptic portion in a patient's eye. The subject IOL is balanced havingpreferably one looped haptic element formed on one edge of the optic andthe other looped haptic element formed on an opposed edge of the optic.However, alternative balanced embodiments having three or four loopedhaptic elements are also considered to be within the scope of thepresent invention. In accordance with the present invention, each of thelooped haptic elements has a broad connecting portion, two radialorientation portions, two spring portions and a linking portionconnecting the two spring portions. The broad connecting portion of eachlooped haptic element is connected to the outer peripheral edge of theoptic portion. Each looped haptic element forms a large fenestration toenhance capsular fixation once within an eye. The looped hapticelements' spring portions and linking portions are designed to engage aninner surface of a patient's eye.

Each looped haptic element's broad connecting portion is designed toachieve optimal optic stability by avoiding tilt and axial displacement.Within these broad connecting portions, each looped haptic element isdesigned to bend in a plane generally perpendicular to the optical axisof an eye rather than in a plane generally parallel to the optical axisof an eye. By providing looped haptic elements with this type offlexibility characteristic, the present IOL tends to have maximizedstability within an eye. The flexibility characteristic of the subjectlooped haptic elements relative to the optic portion eliminatesunacceptable tilting or axial displacement of the optic portion alongthe optical axis when compressive forces are exerted against the loopedhaptic elements of the IOL.

Accordingly, it is an object of the present invention to provideintraocular lenses for use in aphakic or phakic eyes.

Another object of the present invention is to provide intraocular lensesfor use in aphakic or phakic eyes with flexibility characteristics whichmaximize stability thereof.

Another object of the present invention is to provide intraocular lensesfor use in aphakic or phakic eyes, which minimize tilt or axialdisplacement of the optic portions of the lenses along the optical axisof the eyes.

Another object of the present invention is to provide intraocular lensesfor use in aphakic or phakic eyes, which minimize damage to tissues inthe interior of the eyes.

Still another object of the present invention is to provide intraocularlenses, which are resistant to decentration within the eyes.

These and other objectives and advantages of the present invention, someof which are specifically described and others that are not, will becomeapparent from the detailed description, drawings and claims that follow,wherein like features are designated by like numerals.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic representation of the interior of a human eyeincluding a natural lens;

FIG. 2 is a plan view of an IOL with an optic and two looped hapticelements made in accordance with the present invention;

FIG. 3 is a side view of the IOL of FIG. 2;

FIG. 4 is a side view of the IOL of FIG. 2 with sharper peripheral edgeson a posterior surface of the optic;

FIG. 5 is a side view of the IOL of FIG. 2 with sharper edges on the twolooped haptic elements;

FIG. 6 is a side view of the IOL of FIG. 2 with rounder edges on the twolooped haptic elements; and

FIG. 7 is a side view of a looped haptic element of FIG. 2 taken alongline 7—7 with a stiffening element therein.

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 illustrates a simplified diagram of an eye 10 showing landmarkstructures relevant to the implantation of an intraocular lens of thepresent invention. Eye 10 includes an optically clear cornea 12 and aniris 14. A natural crystalline lens 16 and a retina 18 are locatedbehind the iris 14 of eye 10. Eye 10 also includes anterior chamber 20located in front of iris 14 and posterior chamber 22 located betweeniris 14 and natural lens 16. IOLs of the present invention arepreferably implanted into lens capsule 24 or posterior chamber 22 torefract light after a diseased natural lens 16 has been surgicallyremoved (aphakic application). Eye 10 also includes an optical axisOA—OA that is an imaginary line that passes through the optical center26 of anterior surface 28 and posterior surface 30 of lens 16. Opticalaxis OA—OA in the human eye 10 is generally perpendicular to a portionof cornea 12, natural lens 16 and retina 18.

The IOL of the present invention, as best illustrated in FIGS. 2 and 3,is identified by reference numeral 32. IOL 32 is preferably designed forimplantation preferably in lens capsule 24 or posterior chamber 22 of apatient's aphakic eye 10. However, IOL 32 may likewise be implanted inanterior chamber 20 or posterior chamber 22 of a patient's phakic eye10. IOL 32 has an optic portion 34 with an outer peripheral edge 36.Preferably integrally formed on peripheral edge 36 of optic portion 34are two opposed looped haptic elements 38, each having a broadconnecting portion 40, two radial orientation portions 42, two springportions 44 and a linking portion 46. Broad connecting portions 40 arepreferably integrally formed with and permanently connected to outerperipheral edge 36 of optic portion 34. Alternatively however, loopedhaptic elements 38 may be attached to optic portion 34 by staking,chemical polymerization or other methods known to those skilled in theart.

In accordance with the present invention, each looped haptic element 38is designed to preferably engage inner surfaces 48 in lens capsule 24,surfaces 50 in posterior chamber 22 or surfaces 51 in anterior chamber20. Looped haptic elements 38 are designed so that when IOL 32 isimplanted in a patient's eye 10 and held in place through compressiveforces exerted by inner surfaces 48, 50, or 51, looped haptic elements38 flex to accommodate the particular size of eye 10. Looped hapticelements 38 are designed to be resistant to flexing and tilting in aplane generally parallel to that of optical axis OA—OA of eye 10. Bydesigning this type of flexibility characteristic into looped hapticelements 38, IOL 32 may be manufactured in one or a few standard sizesand be a suitable fit for most sizes of patients' eyes 10. Theflexibility characteristic of looped haptic elements 38 also minimizeaxial displacement of optic portion 34 in a direction along optical axisOA—OA of eye 10.

Broad connecting portions 40 of looped haptic elements 38 attach thelooped haptic elements 38 to optic portion 34 of IOL 32. The broadconnecting portions 40 are designed to be broad to increase rigidity andto minimize axial displacement or tilting of IOL 32. Broad connectingportions 40 likewise prevent the snagging or catching of eye 10structures such as the rhexis 52 on optic 34. Each broad connectingportion 40 preferably measures to equal 15 to 35 percent of thecircumference of the optic portion 34. For phakic use, IOL 32 mayoptionally be vaulted at broad connection portions 40 to have anangulation of 0 to 10 degrees but preferably 4 to 5 degrees.

Radial orientation portions 42 of looped haptic elements 38 haveinterior surfaces 54 and exterior surfaces 56. Interior surfaces 54 andexterior surfaces 56 are formed with an outward curve to increase thestability of IOL 32 when implanted in eye 10. Outer ends 58 of radialorientation portions 42 are of a significantly smaller width than thatof radial orientation portions 42 at broad connecting portions 40 tominimize the surface area thereof. The surface area of outer ends 58 isdesigned to be as small as possible to minimize the IOL's 32 contactwith the lens capsule's 24 equatorial germination zone 60 therebydecreasing cellular growth and posterior capsular opacification of IOL32. The width of outer ends 58 is also designed to be smaller than thatof the thickness of looped haptic elements 38 to allow for flexing ofspring portions 44 in a plane perpendicular to optical axis OA—OA of eye10.

Spring portions 44 have an interior surface 62 and an exterior surface64. Spring portions 44 are designed to absorb compressive forces exertedby the eye 10 and maintain IOL alignment within lens capsule 24. Springportions 44 when compressed upon absorption of compressive forces deformwhereby interior surfaces 62 may abut outer ends 58. Also, when placedunder sufficient compressive forces, each spring portion 44 may deflectoutwardly in a direction away from its adjacent spring portion 44 anddownwardly in a direction toward optic portion 34 to absorb such forcesand avoid undesirable flexing and tilting in a plane parallel to theoptical axis OA—OA of eye 10.

Linking portions 46 connect adjacent spring portions 44 to form a loopedhaptic element 38. Linking portions 46 are slightly bowed at preferablyless than 20 degrees but more preferably at less than 10 degrees butgreater than 1 degree outwardly away from optic portion 34. Upon one ormore spring portions 44 being deflected outwardly in a direction awayfrom its adjacent spring portion 44 and downwardly in a direction ofoptic portion 34 when placed under compressive forces, the bow oflinking portions 46 is reduced.

At a midpoint in linking portions 46 are depressions 66 formed in loopedhaptic elements 38 to allow for and ensure proper contact with a plungerportion of an IOL inserter if desired for use in implanting the subjectIOL.

Fenestration 68 defined by interior surfaces 54 and 62, and interiorsurfaces 70 of linking portion 46 enhances fixation of IOL 32 withinlens capsule 24, posterior chamber 22 or anterior chamber 20.

Compressive forces of differing magnitudes within the range ofapproximately 2 to 8 mN exerted against looped haptic elements 38effecting an approximately 2.0 mm in overall length compression of IOL32, such as that caused by differing eye sizes or compressive forces bythe eye 10, results in less than approximately 1.0 mm, but morepreferably less than approximately 0.5 mm and most preferably less thanapproximately 0.3 mm axial displacement or tilting of optic portion 34along optical axis OA—OA in an eye 10. Under like compressive forces,IOLs known in the art result in approximately 2.0 mm axial displacementof the optic portion along the optical axis in the eye, which may damagedelicate tissues therein. The unique design of IOL 32 achievessignificantly minimized axial displacement or tilting of optic portion34 to protect the eye 10 from damage when compressive forces are appliedto eye 10.

The flexibility characteristic of looped haptic elements 38 of IOL 32 asdescribed above is achieved through the unique design thereof. Theexterior surface 72 of linking portion 46 and the exterior surface 64 ofspring portions 44 may be formed with either rounded edges 74 depictedin FIG. 6 for a smoother fit with inner surfaces 48, 50, or 51, or moredefined, sharper edges 76 depicted in FIG. 5 to provide a barrier toprevent cellular migration and growth. Another feature which may beincorporated into the subject lens is a sharper peripheral edge 36 onposterior surface 35 of optic portion 34 as depicted in FIG. 4 toprovide a barrier to prevent cellular migration and growth.

The subject IOL 32 is preferably produced having an optic portion 34approximately 4.5 to 9.0 mm, but preferably approximately 5.0 to 7.0 mmand most preferably 6.0 mm in diameter and approximately 0.5 mm to 1.0mm, but preferably approximately 0.6 to 0.8 mm and most preferably 0.7mm in thickness at peripheral edge 36. The size of optic portion 34 maylikewise vary depending on the intended use, such as a smaller size forhyperopic use. Looped haptic elements 38 increase or decrease in overalllength depending upon the diameter of optic portion 34 so that theoverall length of IOL 32 remains generally consistent. As the diameterof optic portion 34 increases, the overall length of looped hapticelements 38 decrease. Likewise, as the diameter of optic portion 34decreases, the overall length of looped haptic elements 38 increase. Ingeneral, looped haptic elements 38 are formed to be approximately 8.5 to13.5 mm, but preferably approximately 9.0 to 12.0 mm and most preferablyapproximately 10.5 mm in overall length. Such overall length is obtainedmeasuring from a point in the center of one half of broad connectingportion 40 around through the center of looped haptic element 38 to apoint in the center of the other half of the same broad connectingportion 40. The width of looped haptic elements 38 measuring thedistance between the outer tips 80 of spring portions 44 isapproximately 4.5 to 9.0 mm, but preferably approximately 5.0 to 6.5 mmand most preferably 5.5 mm. Looped haptic elements 38 preferably havethe same thickness throughout their entire length which is approximately0.2 to 0.9 mm, but preferably approximately 0.3 to 0.7 mm and mostpreferably approximately 0.55 mm. Looped haptic elements 38 could alsohowever be of varying thickness without departing from the scope of thepresent invention. Spring portions 44 measuring the distance from outerend 58 to exterior surface 64 at linking portion 46 are approximately0.4 to 1.5 mm, but preferably approximately 0.6 to 1.2 mm and mostpreferably approximately 0.8 mm. Radial orientation portions 42 areapproximately 1.6 to 4.5 mm, but preferably approximately 2.0 to 4.0 mmand most preferably approximately 3.0 mm in length measuring from thecenter of broad connecting portion 40 to the center of outer end 58.

The desired flexibility characteristic of looped haptic elements 38 ofIOL 32 may likewise be achieved or enhanced by incorporating astiffening element 82, in the shape of a ribbon, in looped hapticelements 38, as illustrated in FIG. 7. Stiffening elements 82 may bepositioned in looped haptic elements 38 to function in a manner similarto that of an I-beam in construction to prevent axial displacement ortilting along optical axis OA—OA when compressive force is applied tolooped haptic elements 38.

Stiffening elements 82 are formed of a less flexible material than thatof IOL 32. Suitable materials for stiffening elements 82 include but arenot limited to polyamides, polyolefins, high-density polyethylenes,polyesters, nylons, metals or any biocompatible material with suitablestiffening characteristics. Stiffening elements 82 may be used inconjunction with looped haptic elements 38 as described above or incases where a thinner looped haptic design is desired while stillachieving the desired flexibility characteristics.

Suitable materials for the production of the subject IOL 32 include butare not limited to foldable or compressible materials, such as siliconepolymers, hydrocarbon and fluorocarbon polymers, hydrogels, soft acrylicpolymers, polyesters, polyamides, polyurethane, silicone polymers withhydrophilic monomer units, fluorine-containing polysiloxane elastomersand combinations thereof. The preferred material for the production ofIOL 32 of the present invention is either polyethylmethacrylate (PEMA)or a hydrogel made from 2-hydroxyethyl methacrylate (HEMA) and6-hydroxyhexyl methacrylate (HOHEXMA), i.e., poly(HEMA-co-HOHEXMA).Poly(HEMA-co-HOHEXMA) is a preferred material for the manufacture of IOL32 due to its equilibrium water content of approximately 18 percent byweight, and high refractive index of approximately 1.474, which isgreater than that of the aqueous humor of the eye, i.e., 1.46. A highrefractive index, i.e., above 1.33, is a desirable feature in theproduction of IOLs to impart high optical power with a minimum of opticthickness. By using a material with a high refractive index, visualacuity deficiencies may be corrected using a thinner IOL.Poly(HEMA-co-HOHEXMA) is also a desirable material in the production ofIOLs 32 due to its mechanical strength, which is suitable to withstandconsiderable physical manipulation. Poly(HEMA-co-HOHEXMA) also hasdesirable memory properties suitable for IOL use. IOLs manufactured froma material possessing good memory properties such as those ofpoly(HEMA-co-HOHEXMA) unfold in a controlled manner in an eye, ratherthan explosively, to its predetermined shape. Explosive unfolding ofIOLs is undesirable due to potential damage to delicate tissues withinthe eye. Poly(HEMA-co-HOHEXMA) also has dimensional stability in theeye.

Although the teachings of the present invention are preferably appliedto soft or foldable IOLs formed of a foldable or compressible material,the same may also be applied to harder, less flexible lenses formed of arelatively rigid material such as polymethylmethacrylate (PMMA) havingflexible haptics formed either of the same or a different material.

Optic portion 34 of IOL 32 can be a positive powered lens from 0 toapproximately +40 diopters or a negative powered lens from 0 toapproximately −30 diopters. Optic portion 34 may be biconvex,plano-convex, piano-concave, biconcave or concave-convex (meniscus),depending upon the power required to achieve the appropriate central andperipheral thickness for efficient handling.

Optic portion 34 of the subject IOL 32 may optionally be formed with aglare reduction zone 84 of approximately 0.25 to 0.75 mm but morepreferably approximately 0.3 to 0.6 mm and most preferably 0.5 mm inwidth adjacent outer peripheral edge 36 for reducing glare when outerperipheral edge 36 of IOL 32 is struck by light entering eye 10 duringhigh light or at other times when pupil 86 is dilated. Glare reductionzone 84 is typically fabricated of the same material as optic portion34, but may be opaque, colored or patterned in a conventional manner toblock or diffuse light in plane with optical axis OA—OA.

Subject IOL 32 is preferably manufactured by first producing discs froma material of choice as described in U.S. Pat. Nos. 5,217,491 and5,326,506 each incorporated herein in its entirety by reference. IOL 32may then be machined from the material discs in a conventional manner.Once machined, IOL 32 may be polished, cleaned, sterilized and packagedby a conventional method known to those skilled in the art.

Subject IOL 32 is used in eye 10 by creating an incision in cornea 12,inserting IOL 32 in posterior chamber 22 or anterior chamber 20 andclosing the incision. Alternatively, IOL 32 may be used in eye 10 bycreating an incision in cornea 12 and lens capsule 24, removing naturallens 16, inserting IOL 32 in lens capsule 24 and closing the incision.

IOL 32 of the present invention provides for a refractive lens suitablefor use in lens capsule 24, posterior chamber 22 or anterior chamber 20.IOL 32 has looped haptic elements 38 with flexibility characteristicsthat minimize axial displacement or tilting along optical axis OA—OA ofeye 10 thereby preventing decentration of IOL 32, distortion of visionand damage to delicate tissues within eye 10. IOL 32, having theflexibility characteristics described herein is also advantageousbecause one or a few lens sizes suitably fit eyes 10 of most sizes. Byproviding a “universal” lens such as that of the present invention,clinical risks to patients due to improperly sized lenses are minimized.Such clinical risks minimized include pupil ovalization, cornealendothelium damage and poor fixation. Likewise, manufacturers' need toproduce IOLs of many sizes to fit eyes of many sizes is eliminated, thusreducing production and inventory costs associated therewith.Ophthalmologists also benefit from subject IOL 32 in that time is savedby eliminating the need to determine each patient's eye size and costsassociated with maintaining large inventories of varying sized lenses.

While there is shown and described herein certain specific embodimentsof the present invention, it will be manifest to those skilled in theart that various modifications may be made without departing from thespirit and scope of the underlying inventive concept and that the sameis not limited to the particular forms herein shown and described exceptinsofar as indicated by the scope of the appended claims.

We claim:
 1. An intraocular lens to be implanted within an eye generallyperpendicular to the eye's optical axis comprising: an outer peripheraledge defining an optic portion, and two or more balanced looped hapticelements permanently connected to the outer peripheral edge, whereby acompressive force sufficient to effect a 1.0 mm in diameter compressionof said lens results in less than approximately 1.0 mm of axialdisplacement of said optic portion along the eye's optical axis.
 2. Anintraocular lens to be implanted within an eye generally perpendicularto the eye's optical axis comprising: an outer peripheral edge definingan optic portion, and two or more balanced looped haptic elementspermanently connected to the outer peripheral edge, whereby acompressive force sufficient to effect a 1.0 mm in diameter compressionof said lens results in less than approximately 0.5 mm of axialdisplacement of said optic portion along the eye's optical axis.
 3. Anintraocular lens to be implanted within an eye generally perpendicularto the eye's optical axis comprising: an outer peripheral edge definingan optic portion, and two or more balanced looped haptic elementspermanently connected to the outer peripheral edge, whereby acompressive force sufficient to effect a 1.0 mm in diameter compressionof said lens results in less than approximately 0.3 mm of axialdisplacement of said optic portion along the eye's optical axis.
 4. Theintraocular lens of claim 1, 2 or 3 wherein the looped haptic elementsand the optic portion are both formed of a foldable or compressiblematerial.
 5. The intraocular lens of claim 1, 2 or 3 wherein said lensis formed from a material selected from the group consisting of siliconepolymers, hydrocarbon and fluorocarbon polymers, hydrogels, soft acrylicpolymers, polyester, polyamides, polyurethane, silicone polymers withhydrophilic monomer units, fluorine-containing polysiloxane elastomersand combinations thereof.
 6. The intraocular lens of claim 1, 2 or 3wherein said lens is formed from a hydrogel material.
 7. The intraocularlens of claim 1, 2 or 3 wherein said lens is formed from a hydrogelmaterial which is 18 percent by weight water.
 8. The intraocular lens ofclaim 1, 2 or 3 wherein said lens is formed from poly(HEMA-co-HOHEXMA)or PEMA.
 9. The intraocular lens of claim 1, 2 or 3 wherein said lens isformed from a material having a refractive index above 1.33.
 10. Theintraocular lens of claim 1, 2 or 3 wherein said lens is formed from anacrylic material.
 11. The intraocular lens of claim 1, 2 or 3 whereinsaid lens is formed from a silicone material.
 12. The intraocular lensof claim 1, 2 or 3 wherein said looped haptic elements are dimensionedto have a greater thickness in a plane generally perpendicular to theeye's optical axis than in a plane generally parallel to the eye'soptical axis.
 13. The intraocular lens of claim 1, 2 or 3 wherein aglare reduction zone is formed adjacent to the outer peripheral edge ofthe optic portion.
 14. The intraocular lens of claim 1, 2 or 3 whereinsaid looped haptic elements include a stiffening element having agreater resistance to bending in a plane generally parallel to an eye'soptical axis than in a plane generally perpendicular to the eye'soptical axis.
 15. The intraocular lens of claim 1, 2 or 3 wherein thelooped haptic element includes a stiffening element formed from amaterial selected from the group consisting of polyimide, polyolefin,high-density polyester, nylon and metal.
 16. A method of manufacturingthe intraocular lens of claim 1, 2 or 3 comprising: forming a disk of asuitable material, and machining said lens from said disk.
 17. A methodof using the intraocular lens of claim 1, 2 or 3 comprising: creating anincision in a cornea of an eye, and inserting said intraocular lens in aposterior chamber or an anterior chamber of said eye.
 18. A method ofusing the intraocular lens of claim 1, 2 or 3 comprising creating anincision in a cornea and lens capsule of an eye, removing a natural lensof said eye, and inserting said intraocular lens in said lens capsule ofsaid eye.